Cardiovascular modeling is a challenging fluid-structure interaction problem that involves treatment of complex geometries and boundary conditions in order to effectively capture physiological dynamics [1]}. Computational fluid dynamics (CFD) is a widely-used approach for simulating blood flow in the circulatory system [2]}, [3]}, [4]}, [5]}, [6]}, [7]}, [8]}, [9]}, [10]}, [11]}, which includes applications to 1D [10]}, [11]}, [14]}, 2D [15]} or 3D [5]}, [6]}, [7]}, [8]}, [9]}, [21]}, [22]} formulations. The lattice Boltzmann (LB) method [23]}, [24]}, [25]}, [26]}, originating from classical statistical physics, is a powerful alternative to conventional continuum-based CFD methods that use Navier-Stokes equations. The LB method uses simplified kinetic equations combined with a modified molecular-dynamics approach to model both Newtonian and non-Newtonian fluid flow in any complex geometry (the fluid is modeled as particles that stream and collide over a discrete lattice mesh). Indeed, a particular advantage of LB-based hemodynamics solvers is their ability to easily model non-Newtonian effects via its right-hand-side; capturing such effects may be important for small vessels or vessels where the shear rate is low [27]}, [28]}. The accuracy and usefulness of the LB method have been demonstrated in a variety of fluid dynamics problems including turbulence [29]} and multiphase flow [25]}. As highlighted in previous studies [25]}, [26]}, [29]}, [34]}, [35]}, LB methods have been shown to be particularly suitable for hemodynamics simulations since many flow features of clinical interest may require efficient numerical treatment of fully 3D computational domains.
